System and Method for Treating Heart Tissue

ABSTRACT

Some embodiments of a system or method for treating heart tissue can include a control system and catheter device operated in a manner to intermittently occlude a heart vessel for controlled periods of time that provide redistribution of blood flow. In particular embodiments, the system can be configured to provide an estimation of the cumulative effects of the treatment. For example, some embodiments of the system or method can treat myocardium that is at risk of infarction by intermittently altering blood flow in a venous system to induce microcirculation within the myocardium, and can output a cumulative dosage value indicative of a measurement of progress of reducing an infarct size.

TECHNICAL FIELD

This document relates to systems and methods for treating heart tissue,for example, by controlling an intermittent occlusion of venous bloodflow in the heart.

BACKGROUND

The heart muscle receives arterial blood via coronary arteries so thatthe blood passes through and nourishes the heart muscle tissue. In somecases, a blockage in a coronary artery can result in a loss or reductionof blood flow through a portion of the heart muscle tissue, therebycreating an area at risk of ischemic death if the area is not timelyreperfused. The injury of the ischemic heart muscle tissue may also beexacerbated by reperfusion injury from a sudden reperfusion of blood totissue that had been deprived of adequate blood flow. After the blockageis removed or otherwise opened to resume blood flow, the ischemicportion of the heart muscle tissue (such as the reperfusedmicrocirculation) may be damaged to the point that normal blood flowdoes not return through the ischemic portion of the muscle tissue. Someconventional systems attempt to repair or treat the ischemic heartmuscle tissue by supplying the ischemic tissue with blood throughretrograde perfusion. For example, the coronary sinus may be temporarilyoccluded so that the blood therein counterflows back from the coronarysinus through the coronary venous system and toward the ischemic muscletissue that previously did not receive blood from the arterial side. Theocclusion of the coronary sinus causes a pressure increase and, as aresult, a redistribution of venous blood via the respective vein(s) intothe capillaries of the border-zone ischemic muscle tissue so as toimprove the supply of nutrients to that ischemic area. When theocclusion is ceased so that blood exits normally through the coronarysinus, the venous blood is flushed out while the metabolic wasteproducts from the damaged tissue are carried off at the same time.

The combination of repeated venous pressure build-up phases followed bya phase of redistribution of flow and wash-out, often referred to as anintermittent coronary sinus occlusion (“ICSO”) method, might in somecircumstances improve arterial blood demand, improve microcirculation byreducing microvascular obstructions, provide a cardioprotective effect,and reduce ischemic tissue infarct size. When the timing of the ICSOmethod (e.g., the occlusion times and the release times) is controlledbased upon monitored pressure measurements, the method is often referredto as pressure-controlled ICSO, or “PISCO.” A computer-implementedcontrol system may be used to control the timing of when to start andwhen to end, and hence the duration of, the occlusion phases that areperformed during a PICSO method.

SUMMARY

Some embodiments of a system or method for treating heart tissue caninclude a control system and a catheter device that are operated tointermittently occlude a heart vessel for controlled periods of time forpurposes of redistributing blood flow, for example, toward a myocardialischemic area or an area at risk (AAR) of ischemia. In particularembodiments, during the initiation of the treatment, the system can beconfigured to activate the catheter device and monitor patientcharacteristics to confirm that the system is attaining a satisfactorylevel of occlusion so as to provide a desired extent of bloodredistribution. For example, in response to monitoring one or morepatient characteristics after the catheter device is initiallyactivated, the system can be configured to output an indication that thecatheter position is satisfactory or that the catheter position shouldbe adjusted. In some embodiments, during the treatment process, thesystem can be configured to determine and display a parameterrepresenting a cumulative quantity of treatment provided over successiveocclusion periods. In one example, the cumulative quantity that iscalculated by the system can correlate to an estimated amount of AARheart tissue that has been salvaged over the course of treatmentprovided, thereby providing practitioners with real-time feedbackregarding the medical progress of the using the catheter device over thecourse of the successive occlusion periods. As such, the cumulativequantity or the estimated amount of AAR can be displayed and repeatedupdated by the control system over the course of the successiveocclusion periods, which facilitates practitioner to more accuratelydetermine whether to continue or end the treatment process using thecatheter device.

Particular embodiments described herein may include a control system fora system for treating heart muscle tissue. The control system mayinclude a sensor signal input to receive a pressure sensor data signalindicative of a pressure in the coronary sinus at least during two ormore occlusion phases of a coronary sinus occlusion catheter (or anothersensor data signal indicative of a bodily characteristic in the coronarysinus at least during two or more occlusion phases of a coronary sinusocclusion catheter). Also, the control system may include a controlcircuit including memory and a processor. The control circuit may beconfigured to determine, in response to stored data points of thepressure sensor data signal (or another bodily characteristic sensordata signal), a cumulative dosage value indicative of cumulative effectsof coronary sinus occlusion catheter treatment over two or moresuccessive occlusion phases.

In other embodiments, a computer-implemented method may includereceiving a pressure sensor data signal indicative of a coronary sinuspressure after a occlusion catheter has substantially occluding thecoronary sinus during an occlusion phase in a sequence of two or moreocclusion phases. The method may also include calculating a cumulativedosage value indicative of cumulative effects of coronary sinusocclusion catheter treatment over the two or more successive occlusionphases.

In some embodiments, a control system for a system for treating heartmuscle tissue may include a control system and a sensor signal input.The control system may be configured to selectively activate anocclusion device for substantially occluding the coronary sinus duringocclusion phases, and configured to deactivate the occlusion device forsubstantially non-occluding the coronary sinus during release phases.The sensor signal input may be configured to receive a pressure sensordata signal indicative of a pressure in the coronary sinus at leastduring the occlusion phases. The control system may be configured to, inresponse to the pressure sensor data signal during at least one of theocclusion phases, output an alert indicating a recommendation toreposition of the occlusion device of the coronary sinus occlusioncatheter.

In further embodiments described herein, a method may include receivinga pressure sensor data signal indicative of a coronary sinus pressureafter a occlusion catheter has substantially occluded the coronary sinusduring an occlusion phase of an occlusion device positioning test. Themethod may also include storing data indicative of at least pressuremaxima and pressure minima measured during the sequence of multipleocclusion phases. The method may further include, after the occlusionphase of the occlusion device positioning test, calculating a pulsatilepressure parameter. The pulsatile pressure parameter may be calculatedbased at least in part upon the data the pressure maxima and pressureminima measured during the occlusion phase of the occlusion devicepositioning test. The method may also include, in response to detectingthat the pulsatile pressure parameter is less than a minimum thresholdvalue, outputting an alert via a user interface of the control systemindicating a recommendation to reposition of the occlusion catheter inthe coronary sinus.

In some embodiments of a system for treating heart muscle tissue, thesystem may include a coronary sinus occlusion catheter including adistal tip portion comprising an adjustable occlusion device. Also, thesystem may include a control system to selectively activate theocclusion device for substantially occluding the coronary sinus duringocclusion phases, and to deactivate the occlusion device forsubstantially non-occluding the coronary sinus during release phases.The control system may include a sensor signal input to receive apressure sensor data signal indicative of a pressure in the coronarysinus at least during the occlusion phases. The control system may beoptionally configured to determine, in response to stored data points ofthe pressure sensor data signal during each of the occlusion phases, acumulative dosage value. The control system can include a display unitthat optionally shows the calculated cumulative dosage value, anestimated amount of salvaged heart muscle tissue based upon thecalculated cumulative dosage value, or both.

In other embodiments, a method may include receiving a pressure sensordata signal indicative of a coronary sinus pressure after a occlusioncatheter has substantially occluding the coronary sinus during anocclusion phase in a sequence of multiple occlusion phases. The methodmay also include storing data in a computer-readable memory device of acontrol console indicative of at least pressure maxima and pressureminima measured during the sequence of multiple occlusion phases. Themethod may further include, after each occlusion phase in the sequenceof multiple occlusion phases, calculating a cumulative dosage valueindicative of a measurement of progress of reducing an infarct size. Thecumulative dosage value may be calculated based at least in part uponthe data the pressure maxima and pressure minima measured during thesequence of multiple occlusion phases. The method may also include,after each occlusion phase in the sequence of multiple occlusion phases,updating a display of: the calculated cumulative dosage value presentedon a display device of the control console, an estimated amount ofsalvaged heart muscle tissue based upon the calculated cumulative dosagevalue, or both.

In particular embodiments described herein, a system for treating heartmuscle tissue may include a coronary sinus occlusion catheter includinga distal tip portion comprising an adjustable occlusion device. Also,the system may include a control system to selectively activate theocclusion device for substantially occluding the coronary sinus duringocclusion phases, and to deactivate the occlusion device forsubstantially non-occluding the coronary sinus during release phases.The control system may include a sensor signal input to receive apressure sensor data signal indicative of a pressure in the coronarysinus at least during the occlusion phases. Optionally, the controlsystem may be configured to, in response to stored data points of thepressure sensor data signal during at least one of the occlusion phases,output an alert via a user interface of the control system indicating arecommendation to reposition of the occlusion device of the coronarysinus occlusion catheter.

In some embodiments, a method may include receiving a pressure sensordata signal indicative of a coronary sinus pressure after a occlusioncatheter has substantially occluding the coronary sinus during anocclusion phase of an occlusion device positioning test. The method mayfurther include storing data in a computer-readable memory device of anocclusion device control system indicative of at least pressure maximaand pressure minima measured during the sequence of multiple occlusionphases. The method may also include, after the occlusion phase of theocclusion device positioning test, calculating a pulsatile pressureparameter. The pulsatile pressure parameter may be calculated based atleast in part upon the data the pressure maxima and pressure minimameasured during the occlusion phase of the occlusion device positioningtest. The method may further include, in response to detecting that thepulsatile pressure parameter is less than a minimum threshold value,outputting an alert via a user interface of the control systemindicating a recommendation to reposition of the occlusion catheter inthe coronary sinus.

Some of the embodiments described herein may provide one or more of thefollowing benefits. First, particular embodiments of the control systemand catheter device can operate to intermittently occlude the coronarysinus or other heart vessel for controlled periods of time that provideeffective redistribution of blood flow toward ischemic or otherwisedamaged heart muscle tissue. The controlled periods of time may beaccurately calculated by the control system based upon the input signals(for instance, the coronary sinus pressure) detected using the catheterdevice or another sensor device for use with the heart.

Second, some embodiments of the control system and catheter device canbe configured to execute an occlusion device positioning test,preferably during the initiation of the coronary sinus occlusionprocess, to output a user interface communication indicative of whetherthe occlusion device of the catheter is positioned within the coronarysinus to provide a satisfactory level of redistributed blood flow. Insome circumstances, when the occlusion device positioning test indicatesan unsatisfactory level of occlusion is detected (e.g., in response tomonitoring a differential between the systolic and diastolic pressuresin the coronary sinus during an occlusion phase), the control system canoutput a message via a user interface of the control system indicativeof suggested actions to improve the level of occlusion. Such correctiveactions suggested via the user interface of the control system caninclude repositioning the catheter device in relation to the coronarysinus, or switching out the catheter device to a different catheterdevice that has a different size or shape, or the like. Afterimplementing corrective actions, the occlusion device positioning testcan be repeated to until the control system confirms (e.g., via the userinterface of the control system) that the occlusion device is positionedwithin the coronary sinus to provide a satisfactory level ofredistributed blood flow.

Third, particular embodiments of the control system can be configured tomonitor one or more patient characteristics when the catheter device isactivated and deactivated over a period of successive occlusion phasesin the coronary sinus, and can also be configured to calculate acumulative dosage value indicative of a treatment level that has beenadministered to a patient over the course of the successive occlusionphases. Such monitored patient characteristics can include, for example,one or more of: (i) the differential between the systolic and diastolicpressures during the occlusion phase, (ii) the differential between thesystolic pressure plateau of the occlusion phase and the averagenon-occluded pressure, and (iii) the inflation hold time of theocclusion phase. In one non-limiting example, the control system can beconfigured to determine, in response to stored data points of thecoronary sinus pressure measurement during each of the occlusion phases,the cumulative dosage value in units of Pressure³×time (as described inmore detail below). The cumulative dosage value, which in someembodiments herein is referred to as a “PICSO Quantity,” can bedisplayed on the user interface of the control system as a numericalvalue that is repeatedly updated with each new occlusion phase.

Fourth, in some embodiments, the cumulative dosage value determined bythe control system can be used to reasonably estimate an amount of AARheart tissue that has been salvaged over the course of the successiveocclusion phases. As such, some embodiments of the control system can beconfigured to correlate the cumulative dosage value over the course of aPICSO treatment with an estimated efficacy value of the PICSO treatment,which may be optionally displayed via the user interface of the controlsystem. For example, in some embodiments the system can calculate anddisplay an estimated myocardial salvage index (MSI) that indicates howmuch of a heart tissue area at risk for ischemia has been salvaged as aresult of the successive occlusion phases occurring during the PICSOtreatment. In such circumstances, the control system can output to theuser a numerical estimate of the treatment efficacy, which is optionallyupdated in real-time with each new occlusion phase and thereby can beused by the practitioner to make an informed decision on when the PICSOtreatment process should be ceased.

Fifth, in particular embodiments the control system can be configured toprovide clinician operators with additional types of information bywhich improved patient outcomes can be achieved. For example, thedisplay of the PICSO Quantity, the estimated MSI based at least in parton the calculation of the PICSO Quantity, or a combination thereofduring administration of the PICSO treatment can facilitate theadministration of an effective and satisfactory level of treatment bywhich improved patient outcomes can be achieved. The details of one ormore embodiments of the invention are set forth in the accompanyingdrawings and the description below. Other features, objects, andadvantages of the invention will be apparent from the description anddrawings, and from the claims.

DESCRIPTION OF DRAWINGS

FIG. 1 is a perspective view of a system for treating heart tissue,including a catheter device in a non-occluding configuration within thecoronary sinus of a heart, in accordance with some embodiments.

FIG. 2 is a perspective view of the system of FIG. 1, including thecatheter device in an occluding configuration, in accordance with someembodiments.

FIG. 3 is a partial cross-sectional view of a catheter device and aguide member of the system of FIG. 1.

FIG. 4 is a side view of a portion of the catheter device of FIG. 3.

FIG. 5 is a transverse cross-sectional view of a shaft portion thecatheter device of FIG. 3.

FIG. 6 is a perspective view of a portion of the system of FIG. 1.

FIG. 7 is a diagram of a control system of the system of FIG. 6.

FIGS. 8A and 8B are examples of graphical plots of coronary sinuspressure values measured during heart tissue treatments using the systemof FIG. 1.

FIGS. 9A and 9B are front views of a portion of the control system ofFIG. 1, including a graphical user interface of the system of FIG. 1during an occlusion device positioning test.

FIG. 10 is a process flow chart for a method of using the system of FIG.1, in accordance with some embodiments.

FIG. 11 is a graph of a cumulative dosage value (calculated by thesystem of FIG. 1) in comparison to an Estimated MSI.

FIG. 12 is a front view of a portion of the control system of FIG. 1,including a graphical user interface of the system of FIG. 1 thatoutputs updated values of the cumulative dosage value, in accordancewith some embodiments.

FIG. 13 is a process flow chart for a method of using the system of FIG.1, in accordance with particular embodiments.

Like reference symbols in the various drawings indicate like elements.

DETAILED DESCRIPTION OF ILLUSTRATIVE EMBODIMENTS

Referring to FIGS. 1-2, some embodiments of a system 100 for treatingheart tissue can include a coronary sinus occlusion catheter 120 and acontrol system 140 configured to activate the coronary sinus occlusioncatheter 120 to intermittently occlude a coronary sinus 20 of a heart10. The catheter 120 can be configured to adjust between a non-occludingposition (FIG. 1) and an occluding position (FIG. 2) so as tointermittently occlude the coronary sinus and thereby redistributevenous blood flow toward heart muscle tissue 30. In this embodiment, thecoronary sinus occlusion catheter 120 includes a distal tip portion 121and a proximal portion 131 (FIG. 6), which includes a proximal hub 132configured to connect with an external control system 140 (FIG. 6) via anumber of fluid or sensor lines. As described in more detail below, thecontrol system 140 may be employed to operate one or more components atthe distal tip portion 121 of the coronary sinus occlusion catheter 120while also receiving one or more sensor signals that provide dataindicative of a heart performance parameter (e.g., coronary sinuspressure, electrocardiogram (ECG) information, or another measuredparameter indicative of hemodynamic performance of the heart). In someembodiments, the control system 140 is configured to control thecatheter 120 so as to occlude the coronary sinus in accordance with aspecific algorithm for determining a release time for releasing anocclusion phase based at least in part upon data input from a sensor. Inparticular embodiments, as described further below, the control system140 is configured to calculate a cumulative dosage value indicative ofthe cumulative effects of the successive occlusion phases, andfurthermore a user interface 142 of the control system can then displaythe cumulative dosage value (sometimes referred to herein as the “PICSOQuantity”), the Estimated MSI based at least in part on the calculationof the PICSO Quantity, or both. These values determined and output bythe control system 140 during the PICSO treatment can be optionallyupdated in real-time with each new occlusion phase, thereby providingthe practitioner with medically pertinent information that aids thepractitioner in deciding when the PICSO treatment should be ceased.

Briefly, in use, the distal tip portion 121 of the coronary sinusocclusion catheter 120 can be arranged in a coronary sinus 20 of a heart10 and thereafter activated to intermittently occlude the blood flowexiting from the coronary sinus 20 and into the right atrium 11. Duringsuch an occlusion of the coronary sinus 20, the venous blood flow thatis normally exiting from the coronary sinus 20 may be redistributed intoa portion of heart muscle tissue 30 that has been damaged due to blooddeprivation or loss of functional myocardium. For example, the portionof heart muscle tissue 30 can suffer from a lack of blood flow due to ablockage 35 in a coronary artery 40. As a result, the arterial bloodflow to the affected heart muscle tissue 30 via a local artery 41 can besubstantially reduced such that the heart muscle tissue 30 becomesischemic or otherwise damaged. Further, because the arterial blood flowis reduced, the venous blood flow exiting from the local vein 21 islikewise reduced. Other branch veins 22 located at different regionsalong the heart 10 may continue to receive blood flow, thereby creatinga supply of venous blood flow exiting through the coronary sinus 20. Insome embodiments, the coronary sinus occlusion catheter 120 can bedelivered into the coronary sinus 20 and thereafter activated so as tointermittently occlude the coronary sinus 20 (refer to FIG. 2). Such anocclusion can cause the venous blood flow to be redistributed to thelocal vein 21 and then into the portion of heart muscle tissue 30 thatsuffers from a lack of blood flow due to the blockage 35 in the coronaryartery 40. As such, the ischemic or otherwise damaged heart muscletissue 30 can be treated with the redistributed venous blood flow sothat the heart muscle tissue 30 receives an improved supply ofnutrients. (As shown in FIGS. 1-2, the catheter 120 is deployed into thecoronary sinus 20 before the arterial blockage 35 is repaired or removedto restore normal coronary arterial blood flow. However, in alternativeembodiments, the arterial blockage 35 can be repaired or removedimmediately before or contemporaneously during use of the catheter 120to occlude the coronary sinus 20.)

Still referring to FIGS. 1-2, the system 100 may optionally include aguide member 110 that is advanced through the venous system of thepatient and into the right atrium 11. The guide member 110 in thisembodiment comprises a guide sheath having a lumen extending between adistal end 111 (FIG. 1) and a proximal end 112 (FIG. 4). In alternativeembodiments, the guide member 110 can serve as guidance for a guide wirehaving an exterior surface extending between the distal end and theproximal end. Optionally, the guide member 110 includes a steerablemechanism to control the orientation of the distal end so as to steerthe distal end 111 through the venous system and into the right atrium11. Also, the guide member 110 can include one or more marker bandsalong the distal end 111 so that the position of the distal end can bemonitored during advancement using an imaging device.

After the guide member 110 is advanced into the right atrium 11, thedistal end 111 may be temporarily positioned in the coronary sinus 20 orthe coronary sinus ostium. From there, the distal tip portion 121 of thecoronary sinus occlusion catheter 120 can be slidably advanced along theguide member 110 for positioning inside the coronary sinus 20. In theembodiments in which the guide member 110 comprises a guide sheath, thedistal tip portion 121 of the coronary sinus occlusion catheter 120 canslidably engage with an interior surface of the lumen during advancementtoward the coronary sinus 20. In the alternative embodiments in whichthe guide member 110 comprises a guide wire structure, the distal tipportion 121 of the coronary sinus occlusion catheter 120 can slidablyadvance over the exterior surface of the guide wire (e.g., a lumen 125of the catheter 120 passes over the guide wire) during advancementtoward the coronary sinus 20. After the coronary sinus occlusioncatheter 120 reaches the coronary sinus 20, the distal end 111 of theguide member 110 can be withdrawn from the coronary sinus 20 and remainin the right atrium 11 for mechanical support during use of the coronarysinus occlusion catheter 120.

Still referring to FIG. 1, the distal tip portion 121 of the coronarysinus occlusion catheter 120 that is positioned in the coronary sinus 20includes an occlusion device 122, which in this embodiment is in theform of an inflatable balloon device. The occlusion device 122 can beactivated so as to occlude the coronary sinus 20 and thereby causeredistribution of the venous blood into the heart muscle tissue 30 thatis damaged due to a lack of arterial blood flow. As described in moredetail below, the inflatable balloon device 122 can be in fluidcommunication with an internal lumen of the coronary sinus occlusioncatheter 120, which is in turn in communication with a pneumaticsubsystem of the control system 140 (FIG. 6). As such, the controlsystem 140 can be employed to inflate or deflate the balloon device 122in the coronary sinus.

The distal tip portion 121 also includes a one or more distal ports 129that are positioned distally forward of a distal end of the occlusiondevice 122. In the depicted embodiments, the distal ports 129 as definedalong a flexible elongate shaft portion that extends distally forward ofa distal end of the occlusion device 122, and a majority or all of thedistal ports face is a generally radially outward direction and aresubstantially uniformly spaced apart from one another along thecircumference of the distal tip. As described in more detail below, thedistal ports 129 may all be in fluid communication with a single sensorlumen (FIG. 5) extending through the coronary sinus occlusion catheter120. Accordingly, at least one parameter of the coronary sinus (e.g.,the coronary sinus pressure or other parameters indicative ofhemodynamic performance as described below) can be monitored via asensor device in communication with the distal ports 129.

Referring now to FIGS. 3-5, the coronary sinus occlusion catheter 120carries the occlusion device 122 along its distal tip portion 121 whilethe proximal hub 132 is arranged along the proximal portion 131. Aspreviously described, the proximal hub 132 serves as the connectioninterface between a number of fluid or sensor lines 133, 134, and 135(FIG. 3) and the corresponding lumens 123, 124, and 125 (FIG. 5)extending through the catheter 120. In this embodiment depicted in FIG.3, the sensor line 135 is positioned as a central lumen 125 extendingthrough the catheter 120. The sensor line 135 can be configured tocommunicate an input signal indicative of a measured parameter in thecoronary sinus to the control system 140 (FIGS. 6-7). For example, thesensor line can be equipped with a sensor device (e.g., mounted near thedistal ports 129) or otherwise equipped with a communication pathbetween the distal ports 129 and the control system 140. As such, thecatheter 120 can be configured to communicate at least one input signalindicative of a measured parameter in the coronary sinus, such as afluid pressure (e.g., the coronary sinus pressure), a fluid temperature(e.g., using a temperature sensor positioned near the distal ports 129and connected to the control system 140 via the sensor line 135), avolume or mass flow rate or rate of change thereof (e.g., using a flowsensor positioned near the distal ports 129 and connected to the controlsystem 140 via the sensor line 135), an acceleration of the coronarysinus vessel (e.g., using one or more accelerometers positioned alongthe distal tip and connected to the control system 140 via the sensorline 135), a displacement of the coronary sinus vessel (e.g., using anultrasound or optical measuring device to detect the movement of thecoronary sinus vessel during each heartbeat), or another parameterindicative of hemodynamic performance of the heart (e.g., intra coronarysinus or other intra vessel electrocardiogram (ECG), contractilitymeasurements, or the like).

In this particular embodiment, the sensor line 135 of the catheter 120is configured to detect the coronary sinus pressure, which can beaccomplished using a pressure sensor positioned near the distal ports129 or using a fluid-filled path through the sensor line 135. Forexample, at least the sensor line 135 is connected to the proximal hub132 using a Luer lock 137 so as to maintain the fluid path from thecentral lumen 125 of the catheter 120 to the lumen of the line 135.

As previously described, the system 100 may include the guide member 110that is used to direct the coronary sinus occlusion catheter 120 throughthe venous system and into the heart 10. Referring to FIG. 3, the guidemember 110 may be a guide sheath having a central lumen extending from aproximal end 112 (FIG. 4) to a distal end 111 (FIG. 1.) As previouslydescribed, the guide member 110 may be equipped with a steeringmechanism (e.g., steel cables, a shape memory element, or the like) sothat the practitioner can more readily advance the guide member 110through the venous system and into the right atrium.

Still referring to FIGS. 3-5, the occlusion device 122 of the coronarysinus occlusion catheter 120 may comprise an inflatable balloon devicehaving a predetermined shape when in the inflated condition. In thisembodiment, the inflatable balloon device 122 includes a first conicalportion narrowing down toward the distal direction, a second conicalportion narrowing down toward the proximal direction, and a smallgenerally cylindrical rim portion which is arranged between the conicalportions. The narrowed ends of each of the conical portions areconnected with the catheter shaft so as to provide a seal that preventsgas leakage from the balloon device 122. In the inflated condition, thediameter of the balloon device 122 in the region of the cylindrical rimportion is, for example, between about 6 mm and about 40 mm, betweenabout 7 mm and about 25 mm, and preferably about 15 mm. The longitudinallength of the balloon device is, for example, between about 20 mm andabout 30 mm, and preferably about 25 mm. Optionally, the coronary sinusocclusion catheter 120 can be equipped with one or more marker bandspositioned inside the balloon device 122 so as to be rendered visibleduring an interventional procedure by suitable imaging processes.

As shown in FIG. 5, the shaft of the coronary sinus occlusion catheter120 extending distally from the proximal hub 132 can include a pluralityof lumens 123, 124, 125, and 126. In this embodiment, the ringsegment-shaped lumen 123 serves to supply and discharge fluid (e.g.helium or carbon dioxide gas in this embodiment) for inflating andevacuating the balloon device 122. The ring segment-shaped lumen 124,which is smaller than the other lumen 123, likewise communicates withthe interior of the balloon device 122 and serves to measure the fluidpressure within the balloon device 122. The central lumen 125 in thisembodiment is employed for measuring the coronary sinus pressure. Thecentral lumen 125 is in fluid communication with the distal ports 129 ofthe catheter 125 so that the blood pressure in the coronary sinus istransferred to the fluid-filled path extending through the central lumen125 and to the pressure sensor device 136 (FIG. 2). Alternatively, aminiature pressure sensor can be positioned immediate adjacent to thedistal ports 129 such that a sensor wire (e.g., electrical or optical)extends through the central lumen 125 for communication with the controlsystem 140 (FIG. 2). In this embodiment, the shaft of the coronary sinusocclusion catheter 120 includes a fourth lumen 126 having a circularcross section. One or more additional sensors or sensor wires can bepositioned in this fourth lumen. Alternatively, a stiffening wire can bearranged in the fourth lumen 126 so as to extend through the cathetershaft in the region of the balloon device 122. The stiffening wire,which can comprise of a shape memory material such as Nitinol or cancomprise piezo steering/stiffening elements, can be used to facilitatedelivery of the distal tip portion 121 into the coronary sinus 20.

Referring to FIG. 4 in more detail, the distal ports 129 of the catheter120 are arranged distally forward of the distal end of the balloondevice 122 and are oriented to face generally radially outward from theend of the catheter 120. In the depicted embodiments, the distal ports129 as defined along a flexible elongate shaft portion that extendsdistally forward of a distal end of the occlusion device 122, andoptionally, the flexible elongate shaft portion that carries the distalports 129 may extend for a longitudinal length that is greater than thelongitudinal length of the balloon device 122. As such, the distal ports129 of the coronary sinus occlusion catheter 120 can be configured sothat the fluid pressure in the coronary sinus can be accurately measuredeven if a portion of the distal end abuts against the wall of thecoronary sinus or any other vessel. In this embodiment, the distal ports129 comprise three or more ports that are evenly spaced apart along theflexible elongate shaft portion and along a tapered tip, therebyenabling the fluid pressure in the coronary sinus to be applied into oneor more of the ports 129 even if some of the ports 129 are positionedagainst a wall of the coronary sinus.

Referring now to FIGS. 6-7, the control system 140 can be configured toprovide automated control of the occlusion device 122 of the coronarysinus occlusion catheter 120. In some embodiments, the control system140 includes a computer processor that executes computer-readableinstructions stored on a computer memory device so as to activate ordeactivate the occlusion in the coronary sinus 20 in accordance with aparticular process. For instance, the control system 140 can beconfigured to release the occlusions phase (e.g., deflate the occlusionballoon 122 in this embodiment) in the coronary sinus 20 in response toa series of real-time measurements (e.g., coronary sinus pressuremeasurements in this embodiment) detected during the same occlusionphase. In addition, the control system 140 is equipped with a displaydevice 142 having a graphical user interface that provides apractitioner or other users with time-sensitive, relevant dataindicative of the progress of a coronary sinus occlusion procedure andthe condition of the heart 10. As such, the user can readily monitor thepatient's condition and the effects of intermittently occluding thecoronary sinus 20 by viewing the graphical user interface 142 whilecontemporaneously handling the coronary sinus occlusion catheter 120 andother heart treatment instruments (e.g., angioplasty catheters, stentdelivery instruments, or the like). Additionally, the control system 140in this embodiment is configured to calculate a cumulative dosage valueindicative of the cumulative effects of redistributing blood flow overthe course of successive occlusion phases. Preferably, the cumulativedosage value calculated by the control system 140 is useful inestimating an amount of AAR heart tissue that has been salvaged over thecourse of the successive occlusion phases. In such embodiments, the userinterface 142 of the control system 140 can then display the cumulativedosage value, the Estimated MSI based at least in part on thecalculation of the cumulative dosage value, or both. These values outputby the control system 140 during the PICSO treatment can be updated anddisplayed with each new occlusion phase, thereby providing thepractitioner with medically pertinent, time-sensitive information thataids the practitioner in deciding when the PICSO treatment should beceased.

As shown in FIG. 6, the proximal portion 131 of the coronary sinusocclusion catheter 120 and the control system 140 are positionedexternal to the patient while the distal tip portion 121 is advancedinto the coronary sinus 20. The proximal portion 131 includes theproximal hub 132 that is coupled to the control system 140 via a set offluid or sensor lines 133, 134, and 135. As such, the control system 140can activate or deactivate the occlusion component 122 at the distal tipportion 121 of the coronary sinus occlusion catheter 120 while alsoreceiving one or more sensor signals that provide data indicative ofheart performance parameters (e.g., coronary sinus pressure, fluidtemperature in the coronary sinus, volume or mass flow rate, rate ofchange of the volume or mass flow rate, acceleration of the coronarysinus vessel, displacement of the coronary sinus vessel, intra coronarysinus or other intra vessel electrocardiogram (ECG), surfaceelectrocardiogram (ECG) information, contractility, or another measuredparameter indicative of hemodynamic performance of the heart).

The proximal hub 132 of the coronary sinus occlusion catheter 120 servesto connect the plurality of fluid or sensor lines 133, 134, and 135 withthe portion of the coronary sinus occlusion catheter 120 that extendsinto the patient's venous system. For example, the first line 133extending between the control system 140 and the proximal hub 132comprises a fluid line through which pressurized fluid (e.g., helium,another gas, or a stable liquid) can be delivered to activate theocclusion component (e.g., to inflate the inflatable balloon device122). The fluid line 133 is connected to a corresponding port 143 of thecontrol system 140 (e.g., the drive lumen port in this embodiment) sothat the line 133 is in fluid communication with the pneumatic subsystem153 housed in the control system 140 (as shown in FIG. 7). The proximalhub 132 joins the first line 133 with a balloon control lumen 123 (FIG.5) extending through the coronary sinus occlusion catheter 120 and tothe inflatable balloon device 122.

In another example, the second line 134 extending between the controlsystem 140 and the proximal hub 132 comprises a balloon sensor line thatis in fluid communication with the interior of the inflatable balloondevice 122 so as to measure the fluid pressure within the balloon device122. The proximal hub 132 joins the second line 134 with a balloonpressure lumen 122 (FIG. 5) extending through the coronary sinusocclusion catheter 120 and to the inflatable balloon device 122. Thepressure of the balloon device 122 may be monitored by an internalcontrol circuit 155 (FIG. 7) of the control system 140 as part of asafety feature that is employed to protect the coronary sinus 20 from anoverly pressurized balloon device. The balloon sensor line 134 isconnected to a corresponding port 144 of the control system 140 so thata pressure sensor arranged within the control system 140 can detect thefluid pressure in the balloon device 122. Alternatively, the pressuresensor may be arranged in the distal tip portion 121 or the in theproximal hub 132 such that only a sensor wire connects to thecorresponding port 144 of the control system 140.

The proximal hub also connects with a third line 135 extending from thecontrol system 140. As previously described, the third line can serve asthe sensor line that is employed to communicate an input signal (asdescribed above) to the control system 140. In this particularembodiment, the third line 135 comprises a coronary sinus pressure linethat is used to measure the fluid pressure in the coronary sinus bothwhen the balloon device 122 is inflated and when it is deflated. Theproximal hub 132 joins the third line 135 with a coronary sinus pressurelumen 125 (FIGS. 4-5) extending through the coronary sinus occlusioncatheter 120 and to the distal ports 129 that are forward of the balloondevice 122. In this embodiment, the coronary sinus pressure lumen 125and at least a portion of the third line 135 may operate as fluid-filledpath (e.g., saline or another biocompatible liquid) that transfers theblood pressure in the coronary sinus 20 to pressure sensor device 136along a proximal portion of the third line 135. The pressure sensordevice 136 samples the pressure measurements (which are indicative ofthe coronary sinus pressure) and outputs an sensor signal indicative ofthe coronary sinus pressure to the corresponding port 145 of thecontroller system 140 for input to the internal control circuit 155(FIG. 7). As described in more detail below, the coronary sinus pressuredata are displayed by the graphical user interface 142 in a graph form156 (refer to FIG. 7) so that a practitioner or other users can readilymonitor the trend of the coronary sinus pressure while the coronarysinus 20 is in an occluded condition and in an non-occluded condition.Optionally, the graphical user interface 142 of the control system 140can also output a numeric pressure measurement 157 (refer to FIG. 7) onthe screen so that the practitioner can readily view a maximum coronarysinus pressure, a minimum coronary sinus pressure, the mean coronarysinus value, or all values. In some alternative embodiments, thepressure sensor device 136 can be integrated into the housing of thecontrol system 140 so that the third line 135 is a fluid-filled pathleading up to the corresponding port 145, where the internal pressuresensor device (much like the device 136) samples the pressuremeasurements and outputs a signal indicative of the coronary sinuspressure. In further alternative embodiments, the third line 135 caninclude a fiber optic feed line, which extends from a fiber opticpressure sensor at least partially mounted in the catheter tip 129. Thisfiber optic feed line can be connected to a signal conditioningcomponent (mounted in the catheter tip 129 or integrated into thehousing of the control system 140), which may provide the signalconditioning for the optical pressure sensor).

Still referring to FIGS. 6-7, the system 100 may include one or more ECGsensors 139 to output ECG signals to the control system 140. In thisembodiment, the system 100 includes a set of ECG sensor pads 139 (e.g.,three sensor pads in some embodiments) that are adhered to the patient'sskin proximate to the heart 10. The ECG sensors 139 are connected to thecontrol system 140 via a cable that mates with a corresponding port 149along the housing of the control system 140. As described in more detailbelow, the ECG data are displayed by the graphical user interface 142 ina graph form 158 (refer to FIG. 7) so that a practitioner or other usercan readily monitor the patient's heart rate and other parameters whilethe coronary sinus is in an occluded condition and in an non-occludedcondition. Optionally, the graphical user interface 142 of the controlsystem 140 can also output numeric heart rate data 159 (refer to FIG. 7)based on the ECG sensor data so that the practitioner can readily viewthe heart rate (e.g., in a unit of beats per minute). The ECG sensorsignals that are received by the control system 140 are also employed bythe internal control circuit 155 (FIG. 7) so as to properly time thestart of the occlusion period (e.g., the start time at which the balloondevice 122 is inflated) and the start of the non-occlusion period (e.g.,the start time at which the balloon device 122 is deflated). Inaddition, the control system may be equipped with additional ECG sensorsignals capabilities to monitor the intra coronary, intra vessel orintra coronary sinus electrical ECG activity. These signals may beobtained from the coronary sinus occlusion catheter 120 measured at oneor several locations alongside the shaft 139 or at the distal end wherethe distal ports 129 are located. Alternatively, or in addition, the ECGactivity may be provided from another catheter in the heart such as theintra coronary ECG from an arterial vessel 40.

As shown in FIG. 7, some embodiments of the control system 140 includethe internal control circuit subsystem 155 that communicates with thepneumatics subsystem 153. The control circuit subsystem 155 can includeone or more processors 152 that are configured to execute varioussoftware modules stored on at least one memory device 154. Theprocessors 152 may include, for example, microprocessors that arearranged on a motherboard so as to execute the control instructions ofthe control system 140. The memory device 154 may include, for example,a computer hard drive device having one or more discs, a RAM memorydevice, or the like that stored the various software modules.

In some embodiments, the memory device 154 of the control circuitsubsystem 155 stores a graphical user interface software moduleincluding computer-readable instructions for controlling the graphicaluser interface 142. These graphical user interface control instructionsmay be configured to cause the interface 142 (which includes a touchscreen display device in this embodiment) to display: the pressure datagraph 156 indicative of the coronary sinus pressure, the coronary sinuspressure numerical data 157, the ECG data graph 158, the heart ratenumerical data 159, a series of cumulative dosage values calculatedafter each successive occlusion phase (which can be used to provide thePICSO Quantity graph 160 described further in reference to FIG. 12),treatment timers 161, and an Estimated MSI value 162 (which can beupdated after each new occlusion phase as described further in referenceto FIG. 12). Optionally, the graphical user interface can be configuredto display more than the three graphs 156, 158, and 160 on the screen.For example, in some embodiments, the graphical user interface can beconfigured to contemporaneously display four or more different graphs,such as the coronary sinus pressure graph 156, the ECG data graph 158,the PICSO Quantity graph 160, a fourth graph that depicts the arterialpressure as a function of time, and a fifth graph that illustratesanother data output (e.g., the volume of blood flow).

Further, the graphical user interface control instructions stored in thecontrol circuit subsystem 155 may be configured to cause the interface142 to display a number of configurable touch screen buttons 163, 164,165, and 166 that enable the practitioner or other user to selectdifferent menu options or to input patient information or other data. Inaddition, the graphical user interface 142 may be configured to utilizeseveral of the data inputs to display unique determinants of the statusof the procedure such as the PICSO Quantity graph 160 and the EstimatedMSI 162, for example. This information may guide the user to understandwhen the heart is improving based on the therapy provided, and thus tounderstand when to terminate the therapy.

In addition, the graphical user interface control instructions stored inthe control circuit subsystem 155 may be configured to cause theinterface 142 to display a number of one or more alerts (e.g., refer toFIGS. 9A and 9B), which can be in the form of messages or codes. In someembodiments, the determination of which alert condition, if any, shouldbe display can be completed by the patient safety monitoring softwaremodule stored on the memory device 154.

Still referring to FIG. 7, in some embodiments the occlusion phase andrelease phase software module 200 stored on the memory device 154 caninclude computer-readable instructions that, when executed by one of theprocessors 152 (such as an embedded PC), causes the pneumatic subsystem153 to activate or deactivate the balloon device 122 at selected times.The control system 140 can be configured to calculate the time periodsduring which the coronary sinus is in an occluded state and in anon-occluded state and to calculate when each occlusion phase shouldbegin and when each occlusion phase should end in order to achieve amaximum clinical benefit of the desired mode of action, namely, alteredvenous side blood flow that induces microcirculation in a targeted hearttissue. The control system 140 may take into account various monitoredparameters, and make the timing determinations in real-time, such thattiming of each cycle of the method may be appropriate in light ofmonitored parameters.

After the duration of time for the release phase is reached, the processmay start a new occlusion phase. This cyclical process can continue foran extended period of minutes or hours, thereby resulting in numerouscycles of occlusion phases and release phases. Accordingly, in someembodiments, the coronary sinus occlusion catheter 120 (FIGS. 1-2) maycontinue to intermittently occlude the coronary sinus (FIGS. 1-2) tothereby redistribute the venous blood flow to the damaged portion of theheart muscle tissue 30. The overall duration of time for using thecoronary sinus occlusion catheter 120 to provide the multiple occlusionphases may be determined by a practitioner viewing the pertinent datapresented via the user interface 142, including the cumulative dosagevalue, the Estimated MSI (which can be based at least in part on thecalculation of the cumulative dosage value), or both. In someembodiments the control circuit 155 can include computer-readableinstructions stored on the memory device 154 that, when executed by oneof the processors 152, calculates indicators of the status and efficacyof the procedure such as the PICSO Quantity graph 160 and the EstimatedMSI 162. The calculation of the PICSO Quantity values and the EstimatedMSI 162 will be described further below in reference to FIGS. 8A, 8B,and 11. Optionally, the practitioner may rely upon additional factorswhen determining the overall duration of time for using the coronarysinus occlusion catheter 120, including the trend of the input sensorsignals (e.g., the trend of coronary sinus pressure measurements asdisplayed on the user interface 142 of FIG. 7 or a derivate thereof), ameasurement of particular bio-markers present in the patient's blood(e.g., lactate (which increases in the event of ischemia), potassium (anindicator of ischemic tissue), and the like), or a combination thereofor another input signal.

The patient safety monitoring software module stored on the memorydevice 154 can include computer-readable instructions that, whenexecuted by one of the processors 152, causes the control circuitsubsystem 155 to detect if any of the system sensors (e.g., the pressuresensors) output a measurement that is outside of a selected safetyrange. For example, if the coronary sinus pressure signal input to thecontrol system 140 indicates a coronary sinus pressure that is above aselected threshold, the control circuit subsystem 155 can cause thegraphical user interface 142 to display an alert in the form of atextual message or an error code. Further, in some embodiments, thecontrol circuit subsystem 155 may automatically cause the pneumaticsubsystem to deflate the balloon device 122 so as to immediately reducethe high pressure in the coronary sinus 20.

Still referring to FIG. 7, the pneumatic subsystem 153 of the controlsystem 140 can be configured to promptly inflate or deflate the balloondevice 122 in response to the control circuit subsystem. In someembodiments, the pneumatic subsystem may include a reservoir containingpressured gas, such as helium or carbon dioxide, and a vacuum pump. Thereservoir and the vacuum pump can be controlled by a set of valves andare monitored by a set of pressure sensors that feedback into thecontrol circuit subsystem 155. In such circumstances, the pneumaticsubsystem can be configured to inflate or deflate the balloon device 122at the distal tip portion 121 of the coronary sinus occlusion catheter120 in less than 1 second, less that about 0.6 seconds, and preferablyless than about 0.4 seconds.

Referring now to FIGS. 8A and 8B, as mentioned above the control system140 can be configured to receive data from a sensor signal input 212(e.g., a coronary sinus pressure sensor, and the like) and to display onthe graphical user interface 142 a graph of the data such as coronarysinus pressure graph 210. The upper plot on the graph 210 of FIG. 8Aillustrates an example of the changes in coronary sinus pressure overtime during a series of occlusion phases 215 and release phases 225. Thelower plot of FIG. 8A illustrates the time-based derivative of the upperplot, which is the rate of the changes in coronary sinus pressure overtime. FIG. 8B is an enlargement of an occlusion phase 215 that isbordered by preceding and succeeding release phases 225. As will beexplained further below, in some embodiments the coronary sinus pressuredata, from which graph 210 is created, can be used to: (i) confirm thatthe system 100 is attaining an effective and satisfactory level ofocclusion so as to provide a desired quality of treatment and (ii)calculate a PICSO Quantity parameter that can be used to estimate anefficacy of the treatment in terms of an Estimated MSI (myocardialsalvage index).

The control system 140 can be configured to monitor and store at leastportions of the input signals from the sensors being used by the system100. For example, in the embodiment depicted in FIGS. 8A and 8B, thecontrol system 140 is configured to at least store the systolic maxima(e.g., pressure values such as data points 214 a-d and the like) and thediastolic minima (e.g., pressure values such as data points 213 a-d andthe like) of the coronary sinus pressure signal 212 occurring over aseries of consecutive heartbeats during each occlusion phases 215 andeach release phases 225. Based at least partially upon the systolicmaxima data points during the occlusion phase 215 (e.g., data points 214a-c), the control system 140 can be configured to perform a curvefitting operation so as to determine a “curve fit line” or “envelope”curve 216 for the pressure maxima occurring over a series of consecutiveheartbeats during the occlusion phase 215. Similarly, based upon thediastolic minima data points during the occlusion phase 215 (e.g., datapoints 213 a-c), the control system 140 can be configured to perform acurve fitting operation so as to determine a “curve fit line” or“envelope” curve 217 for the pressure minima occurring over a series ofconsecutive heartbeats during the occlusion phase 215. The curve fitlines 216 and 217 can define asymptote or plateau values of the systolicmaxima and diastolic minima. For example, as illustrated in FIG. 8B, thesystolic maxima curve fit line 216 defines a systolic plateau pressure221. Similarly, the diastolic minima curve fit line 217 defines adiastolic plateau pressure 222.

The pressure difference between the systolic plateau pressure 221 andthe diastolic plateau pressure 222 defines a parameter referred toherein as the “pulsatile pressure” 224. In this embodiment, thepulsatile pressure 224 occurring is the coronary sinus during eachocclusion phase 215 can be calculated by the control system 140.Pressure pulses are generated by the heart beating, and higher pulsatilepressures 224 can be indicative of greater levels perfusion to themicrocirculation of the damaged heart muscle tissue 30, which may resultin more effective treatment over the course of successive occlusionphases 215. As will be described further below, the repeatedredistribution of blood of the microcirculation of the damaged heartmuscle tissue 30 can, in some circumstances, salvage or otherwiserestore at least a portion of the myocardial area at risk (AAR) ofinfarction. In this embodiment, the salvage area can be quantifiablyreferred to by the myocardial salvage index (MSI). The efficacy of thetreatment is also influenced by the duration of each occlusion phase215. In this embodiment, the duration of each occlusion phase 215 isalso referred to herein as the “inflation hold time,” which is theperiod of time that the coronary sinus is substantially occluded by anactivated occlusion device (e.g., in this embodiment, the inflatedballoon device 122 of FIG. 2).

The control system 140 can also be configured to calculate a deflationaverage pressure 223 by averaging the systolic maxima and diastolicminima pressures detected during each release phase 225. For example, asshown in FIG. 8B, the diastolic minimum (e.g., data point 213 d and thelike) can be averaged with the systolic maximum (e.g., data point 214 dand the like) during the release phase 225 to calculate a deflationaverage pressure 223. The deflation average pressure 223 is the averagepressure in the coronary sinus during the release phase when thecoronary sinus is not occluded. The difference between the systolicplateau pressure 221 and the deflation average pressure 223 is referredto herein as the global relative pressure drop 226.

When the occlusion of the coronary sinus is released (e.g., whentransitioning from the occlusion phase 215 to the release phase 225),the blood flow that was blocked once again begins to flow in its naturaldirection, rather than tending to redistribute through one or morecardiac veins as during the occlusion phase 215. As the blood begins toflow during the release phase 225, a “washout effect” can take place inthe myocardial areas that were retroperfused as a result of theocclusion phase 215. That is, cellular waste products fromunder-perfused areas of the myocardium that received perfusion as aresult of the occlusion phase 215 can be washed away with the blood asit flows from those areas towards the coronary sinus at the start of andduring the release phase 225. The washout effect may be accentuated bythe global relative pressure drop 226. In some embodiments, the controlsystem 140 can be configured to release the occlusion phase 215 at aparticular time point within a single heartbeat that can provide asignificant washout effect (e.g., to enhance the removal of cellularwaste products after the coronary sinus returns to a non-occludedstate). For example, the control system 140 can monitor the ECG signal149 (FIGS. 6-7) so as to trigger the release of the occlusion phase 215at a time point approximately during a peak contraction of the heart(e.g., during a systolic pressure maximum).

The control system 140 is configured to monitor and store the coronarysinus pressure measurements and (optionally) other bodilycharacteristics (e.g., ECG), which can be used by the control system 140to determine the previously described parameters for each occlusionphase/release phase cycle, including: (i) systolic plateau pressure 221,(ii) pulsatile pressure 224, (iii) global relative pressure drop 226,and (iv) inflation hold time. Optionally, the inflation hold time can beseparately monitored value that is not determined from the coronarysinus pressure measurements.

As described herein, the control system 140 can be configured tocalculate a cumulative dosage value using the coronary sinus pressuremeasurement data. Preferably, the cumulative dosage value calculated bythe control system 140 can be indicative of the cumulative effects ofredistributing blood flow over the course of successive occlusionphases. In some embodiments, the cumulative dosage value calculated bythe control system 140 is useful in estimating an amount of AAR hearttissue that has been salvaged over the course of the successiveocclusion phases. In such embodiments, the user interface 142 of thecontrol system 140 can then display the cumulative dosage value, theEstimated MSI based at least in part on the calculation of thecumulative dosage value, or both. These values output by the controlsystem 140 during the PICSO treatment can be updated and displayed witheach new occlusion phase, thereby providing the practitioner withmedically pertinent, time-sensitive information that aids thepractitioner in deciding when the PICSO treatment should be ceased.

The cumulative dosage value determined by the control system 140 can becalculated using a selected algorithm that provides a numerical valueindicative of the cumulative effects of redistributing blood flow overthe course of successive occlusion phases. For example, the cumulativedosage value determined by the control system 140 can provide anumerical expression of parameters referred herein as the “PICSOQuantity” as follows:

$\begin{matrix}{{{{PICSO}\mspace{14mu} {Quantity}} = {\sum\limits_{n = 1}^{n = {{Total}\mspace{14mu} {PICSO}\mspace{14mu} {Cycles}}}( {{PPP}_{n} \times {GRPD}_{n} \times {IHT}_{n}} )}},} & {{Equation}\mspace{14mu} {\# 1}}\end{matrix}$

-   -   where:    -   PPP=the pulsatile pressure,    -   GRPD=the global relative pressure drop, and    -   IHT=the inflation hold time.        The units of PICSO Quantity are units of (pressure)²×(time). For        example, the units of PICSO Quantity can be “mmHg²-minutes” or        the like. As previously described, the PICSO Quantity calculated        by the control system 140 according to Equation #1 can be used        to reasonably estimate the amount of AAR heart tissue that has        been salvaged over the course of the successive occlusion        phases. For instance, it is believed that in particular        circumstances the PICSO Quantity value provides an approximately        linear relationship with the Estimated MSI (as described in more        detail below in connection with FIG. 11). In an alternative        example, the cumulative dosage value determined by the control        system 140 can provide a numerical expression of parameters        referred herein as the “PICSO Quantity” as follows:

$\begin{matrix}{{{{PICSO}\mspace{14mu} {Dose}} = {\sum\limits_{n = 1}^{n = {{Total}\mspace{14mu} {PICSO}\mspace{14mu} {Cycles}}}( {{SPP}_{n} \times {IHT}_{n}} )}},} & {{Equation}\mspace{14mu} {\# 2}}\end{matrix}$

where:

-   -   SPP=the systolic plateau pressure, and    -   IHT=the inflation hold time;

The units of PICSO Dose are units of pressure multiplied by time. Forexample, the units of PICSO Dose can be “mmHg-minutes” or the like. Insome circumstances, the PICSO value calculated by the control system 140can be an indicator of an approximate amount of AAR heart tissue thathas been salvaged over the course of the successive occlusion phases. Itis envisioned that other combinations of the parameters provided hereincan also be used to mathematically represent the extent and efficacy ofthe treatment provided by system 100.

In the depicted embodiments (FIGS. 1, 7, and 12), the control system 140is configured to calculate and then display the PICSO Quantity valueafter each new occlusion phase 215, which can be output via the userinterface 142 in numeric form, in a graphic plot form, or both (as shownin field 160). A practitioner viewing the user interface 142 is thenenabled to use the PICSO Quantity value to enhance the practitioner'sunderstanding of the efficacy of the treatment provided by system 100.In alternative embodiments, calculated value for PICSO Dose can becalculated and then display as an alternative, or in addition, to thePICSO Quantity value on the graphical user interface 142 of the system100.

Referring to now FIGS. 9A and 9B, in some embodiments the control system140 is configured to perform an occlusion device positioning test, forexample, after the coronary sinus occlusion catheter is initiallyinserted into the coronary sinus and before the automated PICSOtreatment process is initiated. The occlusion device positioning testcan advantageously result in a confirmation or alert message output tothe practitioner via the graphical user interface 142. This positioningstep can be optionally performed to confirm whether a satisfactory levelof occlusion during a sample occlusion phase is being achieved by thesystem 100. The level of occlusion, for example, can refer to thepressures (e.g., systolic maxima and pulsatile pressure) attained in thecoronary sinus when the occlusion device 122 is inflated (refer to FIG.2).

In the depicted embodiment of the system 100 (including the catheterdevice 120), the practitioner can attempt to position the occlusiondevice 122 near the ostium of the coronary sinus so that the peripheryof the occlusion device 122 (when inflated) engages with the inner wallof the coronary sinus, thereby effectively redistributing the venousblood through the cardiac veins. The control system 140 can beconfigured to detect one or more patient characteristics (e.g., in thisembodiment, coronary sinus pressure measurements during a sampleocclusion phase) so as to determine whether the occlusion device 122 islocated in a satisfactory position, and furthermore the control system140 can be configured to alert the user with a suggestion to repositionthe occlusion device 122 in some circumstances. For example, FIG. 9Adepicts an example of when a desirable level of occlusion has not beenattained and an alert message 171 a is output from the control system140. In another example, FIG. 9B depicts an example of when a desirablelevel of occlusion has been attained and a different alert message 171 bis output from the control system 140 to confirm the satisfactoryposition of the occlusion device 122.

As described previously in connection with FIG. 8B, the efficacy of thetreatment provided by system 100 can, in some circumstances, be affectedby measurable pressure-based parameters such as the pulsatile pressure(the systolic plateau pressure minus the diastolic plateau pressure) andthe global relative pressure drop (the systolic plateau pressure minusthe deflation average pressure). Accordingly, after the catheter 120 isinitially positioned in the coronary sinus and during an occlusiondevice positioning test, one or more cycles of occlusion can beperformed to determine and display such parameters, and then the controlsystem 140 can output a determination of whether the position of theocclusion device 122 is satisfactory. If the test cycle(s) indicates anunsatisfactory level of occlusion, the clinician operator may takecorrective actions to improve the level of occlusion prior to continuingto administer the heart tissue treatment process using system 100. Suchcorrective actions can include repositioning the occlusion device inrelation to the vessel, or switching out the occlusion device to adifferent occlusion device that has a different size or shape that maybe more suitable to interface with the patient's anatomy. Afterimplementing corrective actions, the occlusion device positioning testcan be repeated to confirm whether an effective and satisfactory levelof occlusion of the heart vessel has been attained, and if it has notbeen attained the clinician may again take corrective actions to improvethe level of occlusion.

FIGS. 9A and 9B depict examples of the user interface display 142 of thecontrol system 140 after the completion of running the occlusion devicepositioning test to confirm whether a satisfactory level of occlusionhas been attained with the current position of the occlusion device 122in the coronary sinus. FIG. 9A depicts an example of when a satisfactorylevel of occlusion has not been attained, and FIG. 9B depicts an exampleof when a satisfactory level of occlusion has been attained. Prior torunning the occlusion device positioning test, the occlusion device isinstalled in the coronary sinus (or other vessel of the patient if theocclusion is intended for a different region of the body) and the system100 is prepared to administer treatment to the heart tissue of thepatient as described previously. As the occlusion device positioningtest is executed by the control system 140, the occlusion device 122 isactivated by the control system 140 (for either a predetermined periodof time or for a variable period of time controlled by the measuredpressure characteristics during the occlusion phase) and the sensorsignal input 212 a (e.g., a coronary sinus pressure sensor) is monitoredby the control system 140 and displayed on the graphical user interface142 for at least one occlusion cycle. Pressure parameters such as thesystolic maxima and diastolic minima are monitored by the system 100during the occlusion and release phases. From such monitored parameters,other parameters can be calculated (refer to FIG. 8B), such as thesystolic plateau pressure, diastolic plateau pressure, pulsatilepressure 224, deflation average pressure 223, and the global relativepressure drop 226.

In some embodiments, at the completion of the occlusion devicepositioning test, the system 100 can compare the monitored and/orcalculated pressure-based parameters to predetermined target thresholdlevels that are established at pre-selected values that represent asatisfactory level of occlusion. The following example is provided toillustrate this. In some embodiments a threshold level for the pulsatilepressure 224 may be established at a minimum threshold value. Theminimum threshold value for the pulsatile pressure 224 may be a numericvalue selected from a range of 25 mmHg or greater, about 25 mmHg toabout 50 mmHg, and is selected to be 30 mmHg in this particularembodiment.

In such cases, when the occlusion device positioning test results in atest occlusion phase having a pulsatile pressure 224 of less than 30mmHg (the minimum threshold value in this embodiment), the controlsystem 140 is configured to output an alert message 171 a (FIG. 9A) viathe user interface 142 that indicates that a low pulsatile pressure 172a has been detected, and that a repositioning of the occlusion device isrecommended. In this situation, the practitioner may activateconfigurable touch screen button 163 to inform the control system 140 ofthe practitioner's intent to reposition the occlusion device 122 withinthe coronary sinus. Then the clinician may proceed to physicallyreposition the occlusion device 122 and, optionally, restart anotherocclusion device positioning test. Alternative, the practitioner mayactivate configurable touch screen button 164 to inform the system 100of the practitioner's intent to proceed with the PICSO treatment processwithout repositioning the occlusion device 122. Then the clinician mayproceed to physically reposition the occlusion device.

Or, when the occlusion device positioning test results in a monitoredpulsatile pressure 224 that is equal to or greater than the examplethreshold level of 30 mmHg (the minimum threshold value in thisembodiment), the control system 140 can provide an alert message 171 b(FIG. 9B) that indicates that a sufficient pulsatile pressure 172 b hasbeen detected, and that the position of the occlusion device 122 issatisfactory. In this situation, the practitioner may activateconfigurable touch screen button 164 to continue the treatment processbeyond the occlusion device positioning test (without repositioning theocclusion device). While in this example of the occlusion devicepositioning test the pulsatile pressure was used as the determiningpressure value, in other embodiments other pressure-based values orcombinations of values can be used to determine whether the occlusion issatisfactory. For example, in some embodiments the global relativepressure 226 (FIG. 8B) drop can be monitored and compared to apredetermined threshold value and used to make a determination as towhether a satisfactory level of occlusion is attained.

Referring to now FIG. 10, some embodiments of the control system 140 canbe configured to implement a process 300 for determining whether theocclusion device is located in a satisfactory position within thecoronary sinus. In particular implementations, the process 300illustrated in FIG. 10 can be used to output the alert messages 171 a-bas described above in reference to FIGS. 9A and 9B.

At operation 310, the process may include initiating an occlusion devicepositioning test (preferably after the occlusion device 122 of thecatheter 120 is initially placed in the coronary sinus of the patient).Optionally, the occlusion device positioning test can be initiated inresponse to user input of one or more buttons on the touchscreeninterface 142 of the control system 140. The occlusion devicepositioning test in this embodiment includes the performance of at leastone occlusion phase and at least one release phase as automaticallycontrolled by the control system 140. As the occlusion and releasecycle(s) are being performed, process 300 continues to operation 320 inwhich one or more patient characteristics (e.g., pressure-basedcharacteristics in this embodiment, such as the systolic maxima anddiastolic minima pressures in the coronary sinus) are detected andstored by the control system 140. The process 300 may continue tooperation 330, in which the detected pressure-based characteristics fromoperation 320 to calculate one or more pressure-based parameters such asthe pulsatile pressure (which is calculated in this embodiment from thedifference between the systolic plateau pressure and the diastolicplateau pressure during the test occlusion phase). At operation 340, theprocess 300 compares the calculated pulsatile pressure from operation330 to a predetermined pulsatile pressure threshold value. As previouslydescribed, the threshold value for the pulsatile pressure may be aminimum threshold value selected from a range of 25 mmHg or greater,about 25 mmHg to about 50 mmHg. If the calculated pulsatile pressure isless than the predetermined pulsatile pressure threshold value, theprocess 300 proceeds to operation 350. At operation 350, the controlsystem 140 displays an alert message on the graphical user interfacerecommending the repositioning of the occlusion device. In suchcircumstances, the process 300 can return to operation 310 after theocclusion device is repositioned within the coronary sinus. However, ifat operation 340 the calculated pulsatile pressure from operation 330 isgreater than or equal to the predetermined pulsatile pressure thresholdvalue, the process 300 proceeds to operation 360. At operation 360, thecontrol system 140 displays a message on the graphical user interfaceindicating that the occlusion device performance is satisfactory.

Referring to FIG. 11, in some embodiments of the system describedherein, the control system 140 can be configured to not only calculatethe cumulative dosage value (e.g., the “PICSO Quantity” or the “PICSODose” described above), but the control system 140 can also beconfigured to estimate an amount of AAR heart tissue that has beensalvaged over the course of the successive occlusion phases based atleast in part upon the calculated PICSO Quantity value or othercumulative dosage value. For example, the estimated amount of AAR hearttissue that has been salvaged can be characterized according to thepreviously described Myocardial Salvage Index (MSI), which in somecircumstances may have an approximately linear relationship with thePICSO Quantity value calculated by the control system 140. Forinstances, the control system 140 can store an algorithm that determinesthe estimated MSI value from the calculated PICSO Quantity valueaccording to a linear model 410, such as one example linear modeldepicted in FIG. 11. In this example plot, a number of sample datapoints for various PICSO Quantity values during different PICSOtreatment procedures can be plotted, and a linear model 410 is thendetermined using linear regression or another modeling technique. (Inother embodiments, more or different data points beyond the data pointsshown in FIG. 11 can be used to select the relationship model betweenthe PICSO Quantity and the estimated MSI.) From there, the linear model410 can be implemented in the form of an algorithm executed by thecontrol system 140 to thereby provide an estimated MSI value based atleast in part upon the calculated PICSO Quantity value. It should beunderstood from the description herein that, in other embodiments, therelationship model between the estimated MSI and the PICSO Quantityvalue need not be a linear model, but instead may be linear, parabolic,asymptotic, or a combination thereof. In accordance with the teachingsherein, the relationship model can be determined from empirical dataincluding multiple different PICSO procedures, and the relationshipmodel can then be implemented in the form of an executable algorithmstored by the control system 140 so as to output the estimated MSI valueto the practitioner during use of the system 100.

As shown in FIG. 11, for purposes of correlating the calculated PICSOQuantity (Equation #1 above) to the MSI (Equation #3 below) in thisembodiment, the plot in FIG. 11 defines the MSI as the difference of thearea at risk (AAR) minus the resulting infarct size, divided by the AAR.Thus, for purposes of determining the relationship model between thecalculated PICSO Quantity and the estimated MSI (such as the linearmodel 410 depicted in FIG. 11), the MSI for each of the empirical datapoints can be calculated as follows:

MSI=(AAR−IS)/AAR, where:   Equation #3:

-   -   MSI=the myocardial salvage index,    -   AAR=the myocardial area at risk of infarction, and    -   IS=infarct size measured at about 3-4 months after treatment.        The AAR is the percentage of the myocardium that is in danger of        infarction, as viewed for example by MM (magnetic resonance        imaging) during a time period of about less than a week after an        acute occlusion of a coronary artery, or other type of cardiac        event (e.g., unstable angina, STEMI, NSTEMI, heart failure, and        the like). The MSI is a measure of how much of the AAR is        salvaged, and is viewed by MM during a time period of about 3-4        months after treatment. For example, if an individual        experiences an acute occlusion of a coronary artery and an MRI        taken about three days later reveals an AAR of 20%, while a        second MRI four months later reveals an IS of 10% of the total        myocardium, then the MSI is equal to 0.5 (or 50%). In other        words, half of the AAR was salvaged. Similarly, if all of the        AAR is salvaged, the MSI would be one (1.0 or 100%). Or, if none        of the AAR is salvaged, the MSI would be zero (0.0 or 0%).

Still referring to FIG. 11, the plot 400 illustrates that, in somecircumstances, using the system 100 to administer treatment of aparticular PICSO Quantity will tend to provide a particular EstimatedMSI. In this example, the line 410 of chart 400 indicates thatadministering a PICSO Quantity of about 100 mmHg²⁻minutes will tend toprovide an Estimated MSI of about 0.5 (or 50%). Also in this example,administering a PICSO Quantity of about 300 mmHg²⁻minutes will tend toprovide an Estimated MSI of about 0.55 (or 55%).

In some embodiments, the relationship model between PICSO Quantity andEstimated MSI can be implemented as part of an algorithm stored andexecuted by the control system 140 of system 100 such that the controlsystem 140 can contemporaneously calculate the PICSO Quantity and theEstimated MSI based on the operations of the system 100. In particularembodiments, calculated values for PICSO Quantity and Estimated MSI canbe displayed on the graphical user interface 142 of the system 100, andthese two numeric values can be repeatedly updated with each newocclusion phase in the series of occlusion phases during the PICSOtreatment process. A practitioner of the system 100 may use thedisplayed parameters such as PICSO Quantity and Estimated MSI to enhancethe clinician's understanding of the efficacy of the treatment providedby system 100, and to make informed treatment decisions, such as howlong to continue the PICSO treatment.

Referring to now FIG. 12, some embodiments of the control system 140 caninclude the graphical user interface 142 that outputs one or morecumulative treatment parameters such as PICSO Quantity 160 and EstimatedMSI 162. In some circumstances, a practitioner (e.g., an interventionalcardiologist in this embodiment) can readily view the updated values ofthe PICSO Quantity 160 and/or Estimated MSI 162 so as to determine withthe PICSO treatment process can be stopped (for example, when thesufficient level(s) of PICSO Quantity 160 and/or Estimated MSI 162 areobtained).

The control system 140 can be configured to calculate the PICSO Quantity160 and the Estimated MSI 162 using the equations and correlations asdescribed above. For example, the PICSO Quantity 160 parameter can becalculated by the control system 140 using Equation #1 provided above.As previously described, the calculation of PICSO Quantity 160 can bebased on characteristics monitored by the control system 140 including(referring to FIG. 8B): (i) systolic plateau pressure 221, (ii)pulsatile pressure 224, (iii) global relative pressure drop 226, and(iv) inflation hold time. The control system 140 in this embodiment isalso configured to calculate the Estimated MSI 162 based at least inpart upon the PICSO Quantity value or another cumulative dosage value.For example, the control system 140 can calculate the Estimated MSI 162using the predetermined relationship model between PICSO Quantity 160and Estimated MSI 162 (such as the relationship model 410 depicted inFIG. 11 or the like).

In this example embodiment of the graphical user interface 142, thePICSO Quantity 160 is displayed both graphically 160 a and numerically160 b, whereas the Estimated MSI 162 is displayed only numerically. Inalternative embodiments, the Estimated MSI 162 may also be displayedgraphically. Additionally, a predetermined targeted level (as input bythe practitioner or otherwise pre-stored by the control system 140), ora message indicating the attainment of the predetermined targeted level,of PICSO Quantity 160 and/or Estimated MSI 162 may be displayed in someembodiments.

Referring now to FIG. 13, some embodiments of a treatment monitoringprocess 500 can be implemented by the control system 140 to calculateand output the cumulative dosage value (e.g., the PICSO Quantity in thisembodiment), the Estimated MSI, or both. The treatment monitoringprocess 500 can be implemented, for example, to output via the userinterface 142 (and to repeatedly update) the PICSO Quantity andEstimated MSI as illustrated FIGS. 11 and 12.

The process may include operation 510, in which the control system 140controls the coronary sinus occlusion catheter to substantially occludethe coronary sinus for an occlusion time period (e.g., an occlusionphase). As described above, during the occlusion phases (and the releasephases) of the treatment, the control system 140 can monitorpressure-based characteristics in the coronary sinus such as thesystolic pressure maxima and diastolic pressure minima. The controlsystem 140 can be configured to perform a curve fitting operation so asto determine a curve fit line for the systolic pressure maxima anddiastolic pressure minima occurring over a series of consecutiveheartbeats during the occlusion phase. These curve fit lines defineplateau values of the systolic maxima and diastolic minima. The controlsystem 140 can calculate a pulsatile pressure (e.g., item 224 in FIG.8B) which is the difference between the systolic maxima plateau and thediastolic minima plateau. The control system 140 can also be configuredto calculate an average of the systolic and diastolic pressures duringthe release phase, which is the deflation average pressure (e.g., item223 in FIG. 8B). Further, the control system 140 can calculate theglobal relative pressure drop (e.g., item 226 in FIG. 8B), which is thedifference between the systolic maxima plateau and the average of thesystolic and diastolic pressures of the release phase.

The process 500 can also include operation 520, in which the controlsystem 140 calculates the PICSO Quantity parameter or another cumulativedosage value (as described above). In this embodiment, the PICSOQuantity parameter can be calculated by the control system 140 usingEquation #1 above. As described below, an updated PICSO Quantity can becalculated by the control system 140 at least after the completion ofeach occlusion and release cycle. As previously described, the PICSOQuantity value is a cumulative dosage value, and therefore accounts forthe cumulative effects of the successive cycles of occlusion phases andrelease phases during the course of the PICSO treatment (as described byEquation #1).

The process 500 can also include operation 530, in which the controlsystem 140 calculates the Estimated MSI parameter. The Estimated MSIparameter can be calculated by the control system 140 based at least inpart upon the PICSO Quantity value or another cumulative dosage value.For example, the control system 140 can calculate the Estimated MSI 162using the predetermined relationship model between PICSO Quantity 160and Estimated MSI 162 (such as the relationship model 410 depicted inFIG. 11 or the like). As described in more detail below, an updatedEstimated MSI parameter can be calculated by the control system 140 atleast after the completion of each occlusion and release cycle (e.g.,each time the PICSO Quantity value is updated).

The process 500 can also include operation 540, in which the controlsystem 140 outputs on the graphical user interface 142 the currentvalues for PICSO Quantity and Estimated MSI. The display of the PICSOQuantity and Estimated MSI values can be updated at least after eachocclusion and release cycle, or more often in some cases. For example,as shown in FIG. 12, the PICSO Quantity is displayed as 676.4mmHg²-minutes, and the Estimated MSI is displayed as 70.3%. By providinga display of the current PICSO Quantity and Estimated MSI, the controlsystem 140 provides the practitioner with meaningful, time-sensitiveinformation indicative of the progress of the PICSO treatment beingadministered by the system 100. In some situations, the practitioner canmake a decision as to whether to cease or continue administeringtreatment based at least in part on the PICSO Quantity displayed by theuser interface 142, the Estimated MSI displayed by the user interface142, or both. For example, the practitioner may compare the EstimatedMSI to a predetermined target value to evaluate whether to end orcontinue the treatment.

The process 500 may also include operation 550, in which the controlsystem 140 receives user input indicating an end to the treatment usingthe system 100. For example, if the practitioner reviews the PICSOQuantity displayed by the user interface 142, the Estimated MSIdisplayed by the user interface 142, or both, and then decides thatsufficient progress was achieved during the PICSO treatment or that thePICSO treatment should end for other reasons, the practitioner can pressone or more buttons on the touchscreen interface 142 of the controlsystem 140 to indicate that the treatment process should end. In suchcircumstances, the process 500 continues to operation 560, in which thecontrol system 140 ceases the intermittent occlusion phases of thecoronary sinus in response to the user input received at operation 550.From there, the coronary sinus occlusion catheter 120 is deactivated andprepared for withdrawal from the patient's heart.

If no such user input (at operation 550) is received by the controlsystem 140 (e.g., no user input is received within a selected timeperiod), the process 500 can return to operation 510 in which a newocclusion and release cycle is initiated. As such, the process 500 canrepeatedly cycle so as to provide a newly updated PICSO Quantity value(or other cumulative dosage value) and a newly updated estimated MSIvalue for each new occlusion and release cycle.

A number of embodiments of the invention have been described.Nevertheless, it will be understood that various modifications may bemade without departing from the scope of the invention. Accordingly,other embodiments are within the scope of the following claims.

What is claimed is:
 1. A method, comprising: receiving a pressure sensordata signal indicative of a coronary sinus pressure after a occlusioncatheter has substantially occluding the coronary sinus during anocclusion phase in a sequence of multiple occlusion phases; storing datain a computer-readable memory device of a control console indicative ofat least pressure maxima and pressure minima measured during thesequence of multiple occlusion phases; after each occlusion phase in thesequence of multiple occlusion phases, calculating a cumulative dosagevalue indicative of a measurement of progress of reducing an infarctsize, the cumulative dosage value being calculated based at least inpart upon the data the pressure maxima and pressure minima measuredduring the sequence of multiple occlusion phases; and after eachocclusion phase in the sequence of multiple occlusion phases, updating adisplay of: the calculated cumulative dosage value presented on adisplay device of the control console, an estimated amount of salvagedheart muscle tissue based upon the calculated cumulative dosage value,or both.
 2. The method of claim 1, wherein said calculating includescalculating the cumulative dosage value in units of (Pressure)²×(time).3. The method of claim 1, after each occlusion phase in the sequence ofmultiple occlusion phases, calculating the estimated amount of salvagedheart muscle tissue based at least in part upon a predeterminedmathematical relationship between the estimated amount of salvaged heartmuscle tissue and the calculated cumulative dosage value.
 4. The methodof claim 3, wherein the estimated amount of salvaged heart muscle tissuebased at least in part upon a linear relationship between the estimatedamount of salvaged heart muscle tissue and the calculated cumulativedosage value.
 5. The method of claim 1, wherein said updating thedisplay comprises contemporaneously displaying on the display deviceboth the calculated cumulative dosage value and the estimated amount ofsalvaged heart muscle tissue.
 6. A system for treating heart muscletissue, comprising: a coronary sinus occlusion catheter including adistal tip portion comprising an adjustable occlusion device; and acontrol system to selectively activate the occlusion device forsubstantially occluding the coronary sinus during occlusion phases, andto deactivate the occlusion device for substantially non-occluding thecoronary sinus during release phases, wherein the control systemincludes a sensor signal input to receive a pressure sensor data signalindicative of a pressure in the coronary sinus at least during theocclusion phases; and wherein the control system is configured to, inresponse to stored data points of the pressure sensor data signal duringat least one of the occlusion phases, output an alert via a userinterface of the control system indicating a recommendation toreposition of the occlusion device of the coronary sinus occlusioncatheter.
 7. The system of claim 6, wherein the control system outputsthe alert indicative of the recommendation to reposition the occlusiondevice in response to detecting that a pulsatile pressure parameterduring a sample occlusion phase is less than a minimum threshold value.8. The system of claim 6, wherein the control system is configured todetermine, in response to stored data points of the pressure sensor datasignal during each of the occlusion phases, a cumulative dosage valueindicative of a measurement of progress of reducing an infarct size. 9.A method, comprising: receiving a pressure sensor data signal indicativeof a coronary sinus pressure after a occlusion catheter hassubstantially occluding the coronary sinus during an occlusion phase ofan occlusion device positioning test; storing data in acomputer-readable memory device of an occlusion device control systemindicative of at least pressure maxima and pressure minima measuredduring the sequence of multiple occlusion phases; after the occlusionphase of the occlusion device positioning test, calculating a pulsatilepressure parameter, the pulsatile pressure parameter being calculatedbased at least in part upon the data the pressure maxima and pressureminima measured during the occlusion phase of the occlusion devicepositioning test; and in response to detecting that the pulsatilepressure parameter is less than a minimum threshold value, outputting analert via a user interface of the control system indicating arecommendation to reposition of the occlusion catheter in the coronarysinus.
 10. The method of claim 9, further comprising in response todetecting that the pulsatile pressure parameter is greater than or equalto the minimum threshold value, outputting a message via the userinterface of the control system confirming the position of the occlusioncatheter in the coronary sinus is satisfactory.
 11. The method of claim9, further comprising: after outputting the message confirming theposition of the occlusion catheter in the coronary sinus, controllingthe occlusion catheter to intermittently occlude the coronary sinusduring a sequence of multiple occlusion phases; after each occlusionphase in the sequence of multiple occlusion phases, calculating acumulative dosage value indicative of a measurement of progress ofreducing an infarct size; and after calculating the cumulative dosagevalue, updating the user interface of the control system to show updatedvalues for: the calculated cumulative dosage value, an estimated amountof salvaged heart muscle tissue based upon the calculated cumulativedosage value, or both.